CN105246405B - Medical image-processing apparatus and radiographic apparatus - Google Patents
Medical image-processing apparatus and radiographic apparatus Download PDFInfo
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- CN105246405B CN105246405B CN201480020352.1A CN201480020352A CN105246405B CN 105246405 B CN105246405 B CN 105246405B CN 201480020352 A CN201480020352 A CN 201480020352A CN 105246405 B CN105246405 B CN 105246405B
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- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
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- A—HUMAN NECESSITIES
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- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
- A61B6/504—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for diagnosis of blood vessels, e.g. by angiography
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- A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
- A61B6/5217—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data extracting a diagnostic or physiological parameter from medical diagnostic data
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- G06T7/0016—Biomedical image inspection using an image reference approach involving temporal comparison
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Abstract
The medical image-processing apparatus of embodiment has blood-vessel image generating unit and pixel value determination section.Blood-vessel image generating unit obtains the Temporal variation of the concentration of contrast agent based on x-ray imaging image data, be performed a plurality of times based on the x-ray imaging image data being collected into mutually different period generated according to color range have with the concentration of contrast agent become specified conditions when corresponding pixel value the image generation of phase image data handle, to obtain the first and second blood-vessel image data.Pixel value determination section determines or corrects the pixel value or phase of at least one party of the first and second blood-vessel image data, so that the pixel value of corresponding phase is consistent between the first blood-vessel image data and the second blood-vessel image data.
Description
Technical field
Embodiments of the present invention are related to medical image-processing apparatus and radiographic apparatus.
Background technology
As one of the blood vessel camera method in radiographic apparatus, there is known digital subtraction angiography (DSA:
Digital Subtraction Angiography).DSA is the radioscopic image number collected before and after subject injection contrast agent
According to difference (subtraction) image data for diagnosis technology.That is, collecting radioscopic image before contrast agent injects
Data are as mask (mask) image data for generating difference image data.On the other hand, it is received by launching contrast agent
Collect x-ray imaging (contrast) image data.Also, by between x-ray imaging image data and mask images data
Difference processing generates DSA image datas for diagnosis.
If generating such DSA image datas, it can obtain and eliminate in the observation of blood vessel after unwanted shade
Image data.That is, the diagnostic image data for the blood vessel for being contaminated shadow by contrast agent can be depicted selectively.Therefore, energy
The useful image of enough diagnosis of the display to blood vessel.
Existing technical literature
Patent document
Patent document 1：No. 8050474 specifications of U.S. Patent No.
Invention content
The subject that the invention solves
The purpose of the present invention is to provide a kind of medical image-processing apparatus and radiographic apparatus, can treat
Front and back equal different times effectively utilize collected each X ray picture in the case of performing x-ray imaging photography repeatedly
Picture.
Means for solving the problems
The medical image-processing apparatus of embodiments of the present invention has blood-vessel image generating unit and pixel value determination section.Blood
Pipe image production part at least obtains the Temporal variation of the concentration of contrast agent based on x-ray imaging image data, and based on mutual
Image generation processing is performed a plurality of times in the x-ray imaging image data that different period is collected into, to obtain the first vessel graph
As data and the second blood-vessel image data, above-mentioned image generation processing is, according to grayscale or color range, generates to have and be made with above-mentioned
The concentration of shadow agent become specified conditions when corresponding pixel value phase image data.Pixel value determination section is determined or is corrected
The pixel value or phase of at least one party of above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data so that upper
It states between the first blood-vessel image data and above-mentioned second blood-vessel image data, the pixel value of corresponding phase is consistent.
In addition, the medical image-processing apparatus of embodiments of the present invention has blood-vessel image generating unit and difference image life
At portion.Blood-vessel image generating unit at least obtains the Temporal variation of the concentration of contrast agent, and base based on x-ray imaging image data
In the x-ray imaging image data being collected into mutually different period, image generation processing is performed a plurality of times, to obtain first
Blood-vessel image data and the second blood-vessel image data, above-mentioned image generation processing are, according to grayscale or color range, generate have with
The concentration of above-mentioned contrast agent become specified conditions when corresponding pixel value phase image data.Difference image generating unit is given birth to
At it is between above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data, become with the concentration with above-mentioned contrast agent
The difference image data of the corresponding pixel value of difference of the phase of specified conditions.
In addition, the radiographic apparatus of embodiments of the present invention have image collection system, blood-vessel image generating unit with
And pixel value determination section.Image collection system at least collects x-ray imaging image data from subject.Blood-vessel image generating unit base
The Temporal variation of the concentration of contrast agent is obtained in above-mentioned x-ray imaging image data, and based in receipts of mutually different period
Image generation processing is performed a plurality of times in the x-ray imaging image data collected, to obtain the first blood-vessel image data and second
Blood-vessel image data, above-mentioned image generation processing is, according to grayscale or color range, generating, there is the concentration with above-mentioned contrast agent to become
Specified conditions when corresponding pixel value phase image data.Pixel value determination section determines or corrects above-mentioned first vessel graph
As the pixel value or phase of at least one party of data and above-mentioned second blood-vessel image data so that in above-mentioned first blood-vessel image
Between data and above-mentioned second blood-vessel image data, the pixel value of corresponding phase is consistent.
Description of the drawings
Fig. 1 is the radiographic apparatus of embodiments of the present invention and the structure chart of medical image-processing apparatus.
Fig. 2 is to indicate the vasotropic side for flowing into moment or arrival time of concentration distribution identification contrast agent based on contrast agent
The figure of method.
Fig. 3 be corresponding to the maximum value that indicates to the concentration distribution of contrast agent when phase partitioning color range first case
Figure.
Fig. 4 is the figure for indicating the color matching example of color range shown in Fig. 3 (C).
Fig. 5 be corresponding to the maximum value that indicates to the concentration distribution of contrast agent when phase partitioning color range second case
Figure.
Fig. 6 is the figure for indicating the color matching example of color range shown in Fig. 5 (C).
Fig. 7 is the figure of the example for the parametrization image for indicating to generate in parametrization image production part shown in FIG. 1.
Fig. 8 is the color range used in the generation indicated according to past first blood-vessel image data, decision or amendment second
The figure of the example of the pixel value of blood-vessel image data.
Fig. 9 is to indicate to make the color in specified position or region in the first blood-vessel image data and the second blood-vessel image data
Between consistent example figure.
Figure 10 is second indicated using the first position and the second blood-vessel image data with the first blood-vessel image data
A part for the concentration distribution of the corresponding contrast agent in position seeks the figure of the example of the phase difference between concentration distribution.
Figure 11 is to indicate to make the color in 2 specified positions or region in the first blood-vessel image data and the second blood-vessel image
The figure of consistent example between data.
Figure 12 is the when phase region for indicating to make to respectively specify that between the first blood-vessel image data and the second blood-vessel image data
Between in solid colour example figure.
Figure 13 is the action for indicating radiographic apparatus shown in FIG. 1 and the processing in medical image-processing apparatus
Flow chart.
Specific implementation mode
For the medical image-processing apparatus and radiographic apparatus of embodiments of the present invention, carried out with reference to attached drawing
Explanation.
Fig. 1 is the radiographic apparatus of embodiments of the present invention and the structure chart of medical image-processing apparatus.
Radiographic apparatus 1 has camera chain 2, control system 3, data processing system 4 and operation bench
(console)5.Camera chain 2 has X-ray tube 6, X-ray detector 7, C-arm 8, base station 9 and diagnostic bed 10.In addition,
Data processing system 4 has A/D (analog to digital：Modulus) converter 11, medical image-processing apparatus 12, D/A
(digital to analog：Digital-to-analogue) converter 13 and display device 14.In addition, A/D converters 11 also sometimes with X-ray
7 integration of detector.
X-ray tube 6 and X-ray detector 7 by clip diagnostic bed 10 it is arranged opposite in a manner of be fixed on the two of C-arm 8
End.C-arm 8 is kept by base station 9.Base station 9 has motor 9A and rotating mechanism 9B, passes through motor 9A's and rotating mechanism 9B
Driving, can make X-ray tube 6 and X-ray detector 7 and C-arm 8 together as propeller high speed rotation to desirable
Position.
As X-ray detector 7, area detector (FPD can be used:Flat panel detector) or image increasing
Strong device TV (I.I.-TV:image intensifier TV).In addition, the outlet side of X-ray detector 7 and data processing system
The A/D converters 11 of system 4 connect.
Control system 3 be by constitute camera chain 2 each integral part output control signal by camera chain 2 into
The device of row drive control.Control system 3 is connect with the operation bench 5 as input unit, can be inputted from operation bench 5 to control
The instruction information of the imaging conditions of system 3 etc..
Also, camera chain 2 is configured to, from rotatable X-ray tube 6 towards being placed under the control of control system 3
Diagnostic bed 10 subject O with mutually different angle successively radiation X ray, can successively be collected using X-ray detector 7 from
Multiple directions have transmitted the X-ray of subject O as X-ray projection data.The x-ray projection being collected by X-ray detector 7
Data are output to A/D converters 11 as X-ray image data.
In addition, being placed near diagnostic bed 10 subject O, it is provided with for injecting making for contrast agent to subject O
Shadow agent injection device 15.Also, by injecting contrast agent from contrast medium injection apparatus 15 to subject O, subject O can be carried out
X-ray imaging photography.For contrast medium injection apparatus 15, can also be controlled by control system 3.
Then, the structure and function of medical image-processing apparatus 12 are illustrated.
The input side of medical image-processing apparatus 12 is connected to the outlet side of A/D converters 11.In addition, at medical imaging
The outlet side for managing device 12 connects display device 14 via D/A converters 13.In addition, medical image-processing apparatus 12 and manipulation
Platform 5 connects.Also, it by the operation of operation bench 5, can in data handling be needed to the input of medical image-processing apparatus 12
Indicate information.
Alternatively, it is also possible to handle dress different from medical imaging built-in in such radiographic apparatus 1 illustrated in Fig. 1
12 are set, and is connect with radiographic apparatus 1 via network using same medical image-processing apparatus as independent system.
Medical image-processing apparatus 12 has video memory 16, subtracts portion shadow (subtraction) 17, filtering part 18, imitates
Penetrate transformation component 19, greyscale transformation portion 20 and parametrization image production part 21.Parameterizing image production part 21 also has phase true
Determine portion 22, color coding unit 23, color range adjustment section 24, colour synchronisation display processing portion 25 and phase difference image making portion 26.
Medical image-processing apparatus 12 with such function can handle journey by making computer read in medical imaging
Sequence is built.But circuit can also be utilized in order to constitute medical image-processing apparatus 12.
Video memory 16 is the storage device for preserving the X-ray image data being collected by camera chain 2.Cause
And if carrying out X-ray in a manner of non-radiography, the X-ray image data of non-radiography is saved in video memory
16, if contrast agent is injected subject O to carry out X-ray, x-ray imaging image data is saved in image storage
Device 16.
Subtracting shadow portion 17 has following function, i.e.,：Generation passes through the radioscopic image of the non-radiography read in from video memory 16
Difference (subtracting shadow) between data and the x-ray imaging image data of time series handles and depicts radiography blood vessel, time
The DSA image datas of sequence.
Filtering part 18, which has to execute high frequency emphasis filtering, low-pass filtering to arbitrary data and smooth filtering etc., wishes
The function being filtered of hoping.
Affine transformation portion 19 has expansion, the contracting that X-ray image data is executed according to the instruction information inputted from operation bench 5
Small, moving in rotation and the function of moving in parallel equiaffine conversion process.
Greyscale transformation portion 20 has with reference to LUT (Look Up Table：Look-up table) carry out X-ray image data gray scale
The function of transformation.
Parametrization image production part 21 has to be taken according to the DSA image datas or x-ray imaging image data of time series
It obtains the function of the time change of the concentration of contrast agent and generates function of the parametrization image data as blood-vessel image data,
The parametrization image data has and becomes the time of specific condition corresponding pixel value with the concentration of contrast agent.Parameterize image
The phase of each location of pixels when data are to specific conditions such as the concentration become the maximums of contrast agent is assigned with and phase phase
Phase image data made of the pixel value for the color answered.
Therefore, there is phase determining section 22 distribution according to the time change for the concentration for indicating contrast agent to determine contrast agent
Concentration becomes the function of the phase of specific condition.In addition, there is color coding unit 23 distribution to be determined with phase determining section 22
When corresponding color function.Color range adjustment section 24 has the color for determining to be used in the color coding of color coding unit 23
The function of rank.
According to the concentration of time point corresponding contrast agent that flows into or reach blood vessel of interest with contrast agent or opposite
The concentration etc. of contrast agent corresponding with the time point that contrast agent is flowed out from blood vessel of interest, can determine according to diagnostic purpose
Specific condition for distributing color.For example, the phase as specific condition can be set as the concentration of contrast agent as most
The time of big value, the regulated proportion of maximum value or threshold value.
Fig. 2 is the concentration distribution indicated according to contrast agent, and identification contrast agent is vasotropic to flow into moment or arrival time
The figure of method.
In Fig. 2, horizontal axis shows that phase direction, the longitudinal axis illustrate that the DSA image datas or contrastographic picture of contrast medium concentration
The intensity of the picture signal of data.As shown in Figure 2, if the DSA image datas or image data of concern time series
Pixel (pixel) corresponding with angiosomes, then can obtain the concentration change profile of contrast agent as signal strength when
Between the upper curve changed.
Typical concentration change profile is to be worth with the inflow of contrast agent and gradually increase, be worth with the outflow of contrast agent
The curve gradually decreased.Thus, it, can if being used for the threshold value TH of the rising of detection curve to the value setting of concentration change profile
Enough identification contrast agent start phase to the inflow of blood vessel of interest, and the concentration as contrast agent reaches the phase Tth of threshold value TH.
But in the case where noise is larger, it is possible to which accidentally the inflow of identification contrast agent starts phase.Accordingly it is also possible to
The regulated proportion of 5 percent to 10 range of the maximum value of the concentration distribution of contrast agent is set as threshold value, to inhibit
The influence of noise.Alternatively, reaching the phase of blood vessel as contrast agent, can also be detected as shown in Figure 2 according to concentration distribution
The phase Tmax of the concentration become the maximum MAX of the contrast agent or 50 percent phase T for reaching maximum value MAXmax/2.With
Under, mainly to be illustrated in case of the arrival phase for recognizing contrast agent.
If to whole pixels execute the phase based on the concentration distribution of contrast agent as shown in Figure 2 it is determining and distribute with
The identified corresponding color of phase, then can generate and depict each blood vessel with color corresponding with the arrival time of contrast agent etc.
Made of parameterize image data.
But it is also possible to by rolling averageization handle to the pixel for representing multiple pixels seek contrast agent concentration when
Between change.That is, can be with smoothing techniques, it will be as the matrix of the image data of the object for the concentration variation for seeking contrast agent
Size reduction.In addition it is also possible to according to the image data for eliminating noise by low-pass filtering treatment, the concentration of contrast agent is sought
Variation.This can also be the rolling average processing carried out to the concentration distribution of the contrast agent on direction in space and low-pass filtering
Processing.
Rolling average processing and low-pass filtering treatment are not limited to direction in space, can also execute in the direction of time.
Rolling average is handled and in the case that low-pass filtering treatment executes in the direction of time, to the contrast agent on time orientation
Concentration distribution execute processing.
Thus, it is possible to according to the rolling average of at least one party of time orientation and direction in space treated contrast agent
Concentration-time changes, and generates parametrization image data.Furthermore it is possible to according at least one party's of time orientation and direction in space
The concentration-time of contrast agent after low-pass filtering treatment changes, and generates parametrization image data.Thereby, it is possible to generate to eliminate to make an uproar
The smooth parametrization image data of sound.
Additionally it is possible to according to the concentration with the contrast agent with the interval photography for being equivalent to x-ray imaging image data
Sampling interval changes compared to shorter data break, contrast agent concentration-time, generates parametrization image data.It can pass through
Interpolation processing is handled using curve matching (curve fitting) processing or center of gravity calculation processing for determining function etc. is arbitrary,
To obtain the concentration-time variation of the contrast agent with the data break shorter than the concentration sample interval of contrast agent.Thereby, it is possible to
More precisely recognize the arrival time etc. of the contrast agent in each pixel.In particular, carrying out rolling average processing and low pass
It is more efficient in the case of at least one party being filtered.
Fig. 3 be corresponding to the maximum value that indicates pair with the concentration distribution of contrast agent when phase partitioning color range first case
Figure.
Fig. 3 (A) indicate according to two-dimensional each position (xi, yj) (i=1,2,3 ..., m；J=1,2,3 ..., n) on make
The arrival phase Tmax (xi, yj) of the concentration distribution of shadow agent and the maximum value MAX of concentration distribution and the contrast agent of determination.It is making
Position near the injection phase of shadow agent, contrast agent relatively early reach.Thus, when identified phase also becomes relatively early
Phase.On the other hand, in the injection phase remote position away from contrast agent, the arrival time of contrast agent becomes late relatively.Thus, institute is really
Fixed phase also becomes relatively late phase.
Fig. 3 (B) indicate to it is determining as shown in Fig. 3 (A) when phase partitioning color range example.As shown in Fig. 3 (B),
During until the slave initial time to finish time changed to the concentration-time of the contrast agent obtained as concentration distribution
Tall distributes the variation of the pixel value for the color being made of R values, B values and G values, so as to make color range.That is, by right
The continuity variation of Tall distribution form and aspect during until slave initial time to finish time of the concentration-time variation of contrast agent,
Color range can be made.
It sets each other off also, according to such color range shown in Fig. 3 (B), when can be by the two dimension for the arrival phase for indicating contrast agent
(time phase map) is penetrated to be color coded.In such manner, it is possible to correspondingly with different when generating the arrival from contrast agent
Color, which is depicted, parameterizes image data made of blood vessel.
But as shown in Fig. 3 (A), the arrival phase Tmax (xi, yj) of contrast agent between location of pixels (xi, yj)
Difference it is relatively small for the range of color range in the case of, the color change between location of pixels (xi, yj) also becomes micro-
It is small.Therefore, it is difficult to distinguish blood vessel by the difference of color sometimes.
In particular, the case where carrying out X-ray for the purpose of by the diagnosis of dural arteriovenous fistula or cerebral arteriovenous malformation
Under, the blood flow observed between artery and vein is important.Thus, when needing to distinguish the arrival of contrast agent in many cases
The smaller multiple blood vessels of difference carved.
It therefore, also can be in color range adjustment section 24 in the case that the difference of the arrival time of contrast agent is smaller in multiple blood vessels
Middle change color range, enabling distinguish blood vessel as the difference of color.Fig. 3 (C) indicates to change the concentration-time of contrast agent
Slave initial time to finish time until during Tall repeated dispensing form and aspect continuity become be turned to pixel value variation,
To make the example of color range.That is, the continuity period of change of form and aspect can be made repeatedly made of color range.
Can initial with concentration distribution specified by the operation by operation bench 5 when corresponding pixel value, pixel value
The cycle T scale of variation and the original pixel values in cycle T scale, to make such color range shown in Fig. 3 (C).As a result,
It can make using specified initial pixel value and specified cycle T scale and the variation of pixel value is concatenated to form
Color range.Further, it is possible to carry out such color matching shown in Fig. 3 (B) in identical cycle T scale.Specifically, can make
Make the color range that the form and aspect in maximum value in 1 cycle T scale change between red, green and basket.
Fig. 4 is the figure for indicating the color matching example of color range shown in Fig. 3 (C).
In Fig. 4,3 orthogonal axis indicate R values, G values and B values respectively.Along as shown in Figure 4 with the maximum value of R values,
The maximum value of G values and the maximum value of B values are the side of the color triangle on vertex, when can determine with each in cycle T scale
Corresponding R values, G values and B values.That is, can be matched colors so that when relative instant is zero and Tscale, G values and B values
Be zero and R values it is maximum value, when relative instant is Tscale/3, R values and B values are that zero and G values are maximum value, opposite
When moment is 2Tscale/3, R values and G values are that zero and B values are maximum value.
If carrying out such color matching, can generate with phase rearward, color from it is red through green variation be blue and return again
To red parametrization image data.In addition, about the color between red, green and basket, for example, can be with R values, G values and B values
The mode of linear change is allocated phase.Alternatively, also can be with the point connection on the center and side by color triangle
R values, G values and B values are distributed to phase by the mode of the angle linear change of line segment.
If the color range made according to color matching in this way generates parametrization image data, even if contrast agent arrives
Difference up to the moment is small, can be used as the difference of color to distinguish blood vessel.That is, when can hold the arrival of contrast agent in detail
It carves.
In addition, attractive color is red.Thus, it is as the example shown in Figure 4, the arrival time of contrast agent is earliest
The color settings of initial phase are red, are improved so as to cause identity.That is, by color range with it is initial when corresponding color value set
Maximum value for R values is effective.Furthermore, as another example it is sub, initial phase is adjusted so that the phase of concern is also as red
Useful.
Fig. 5 be corresponding to the maximum value that indicates pair with the concentration distribution of contrast agent when phase partitioning color range second case
Figure.
Fig. 5 (A) is shown in the same manner as Fig. 3 (A) according to two-dimensional each position (xi, yj) (i=1,2,3 ..., m；J=1,
2,3 ..., n) on the concentration distribution of contrast agent and the maximum value MAX of concentration distribution and the contrast agent of determination arrival phase
Tmax(xi,yj)。
Further, it is possible to will be during until slave initial time to finish time to the time change of the concentration of contrast agent
Tall be assigned with the variation of the pixel value of color, the color range as shown in Fig. 5 (B) be changed to color range shown in Fig. 5 (C).
Color range shown in Fig. 5 (C) is made by being turned to the variation of pixel value to the continuity change for distributing form and aspect during specifying
's.During can be by the specified variation for starting phase T1 and end phase T2 to determine distribution pixel value.It can pass through
From being selected in the x-ray imaging image or DSA images of time series, start phase T1 and terminate phase T2's
It is specified.
Fig. 6 is the figure for indicating the color matching example of color range shown in Fig. 5 (C).
3 orthogonal axis indicate R values, G values and B values respectively in Fig. 6.It is same as Fig. 4, it can be along color triangle
Side, R values, G values and the B values corresponding to each phase in a period of decision is specified.That is, as the example shown in Figure 4, Neng Goujin
Row color matching is starting phase T1 and is terminating phase T2 so that be maximum value to start phase T1, G value and B values be zero and R values
Between intermediate phase, R values and B values are that zero and G values are maximum value, at the end phase T2, and R values and G values are that zero and B values are
Maximum value.
If carrying out color matching as shown in Figure 6, it can be produced on and start between phase T1 and end phase T2 in maximum
The form and aspect of value are in color range that is red, changing between green and blue.That is, can be produced on it is specified in a period of color be through green variation from red
Blue color range.
During other than during specified, can distribute from it is specified during in the variation of pixel value it is different
Pixel value.For example, the inside and outside Colour posture change during specified by enabling to.As a more specific example, color can be made
Rank starting the pervious phases of phase T1 from Bai Xianghong so that change, phase later phase T2 is from indigo plant to leucismus at the end
Change.
Additionally it is possible to for during other than during specified, distribution with it is specified during in transmitance not
Same transmitance.As concrete example, color range can be made so that starting the pervious phases of phase T1, transmitance is from maximum value
Become cancellation, at the end phase later phase T2, it is maximum value that transmitance changes from zero.That is, can be during specified
Transmitance is set to change in defined range in outer phase.In this case, the color value about R values and B values etc., can also make
It does not change outside during specified.
In this way, about outer phase range during specified, can make the pixel value comprising R values, G values and B values with
And at least one party's variation of transmitance in a period of specified compared with change.
The color range after such change shown in Fig. 3 (C) and Fig. 5 (C) can also be made dynamically to change.Specifically, energy
Enough by making the phase of the variation of the pixel value of such color range shown in Fig. 3 (C) or Fig. 5 (C) and at least one party in period become
Change, to make multiple color ranges.So that the phase change of the variation of pixel value is equivalent to makes color range be offset up in phase side.Another party
Face, so that the mechanical periodicity of the variation of pixel value is equivalent to makes color range stretch on phase direction.
If the color for being carried out parametrization image data using the different multiple color ranges of matching colors in this way is encoded, generate with it is multiple
The corresponding multiple parameters image data of color range.Further, it is possible to make the multiple parameters image data of generation on color range direction
It is shown as dynamic image.That is, can change according to the phase of the variation by making pixel value and at least one party in period
And the multiple color ranges made, image blood vessel data is generated as dynamic image.Thereby, it is possible to more easily hold contrast agent and
The flowing of blood flow.In particular, human eye is high to red identity, if so making from phase T1 at the beginning of concern to end phase T2
Until it is red carry out mobile dynamic image, then the blood flow dynamic of region-of-interest should be readily appreciated that.
It can make as shown in Fig. 5 (C) in the case where making color change in during specified as concrete example
With it is each when corresponding Color time change.Even in this case, same phase, color also it is red, green and it is blue it
Between change.In addition, for other than during specified, can make phase T1 from the outset and terminate phase T2 it is assorted respectively gradually
Gradual change turns to white, or transmitance is made to change.
On the other hand, in the case where periodically making the color range of color value variation, by making the initial face in the period
Color value changes gradually, can make multiple color ranges.
Including the color value of R values, G values and B values can also be changed to the value other than maximum value.If that is, by above-mentioned
Color range generates parametrization image data, then the value of the concentration distribution of contrast agent does not have as zero bys low-pass filtering treatment etc.
The brightness value of pixel becomes maximum.That is, the concentration independent of contrast agent, about the pixel that contrast agent reaches, brightness value becomes
For maximum.
Therefore, in order to hold the concentration of contrast agent, it is capable of the brightness value of change parameter image data.In other words,
As blood-vessel image data, the contrast medium concentration having with when the specified conditions such as the concentration become the maximum of contrast agent can be generated
The parametrization image data of corresponding brightness value.
If specifically, maximum R values, G values and the B values of brightness value before changing are set to R0,G0,B0, then can
R values, G values and B values as shown in formula (1) by being multiplied by coefficient k to determine after brightness value change.
(R, G, B)=(kR0,kG0,kB0) (1)
In formula (1), coefficient k is set to corresponding with the concentration of contrast agent zero or more and 1 the following value.Coefficient k is for example
It can be determined by formula (2).
K=P (x, y)/P0 (2)
Wherein, in formula (2), P (x, y) is and the image signal value as x-ray imaging image data or DSA image datas
And the corresponding value of specified conditions such as maximum value of concentration distribution of contrast agent at the position (x, y) obtained, P0It is constant.
If setting coefficient k by formula (2), coefficient k becomes proportional with the value P (x, y) of the concentration distribution of contrast agent
Value.Thus, about the brightness value (R, G, B) of parametrization image data, it can also be set as the value P with the concentration distribution of contrast agent
(x, y) proportional brightness value.Furthermore it is possible to make the pixel of a concentration of noise level of contrast agent or actually produce noise
Pixel brightness value it is fully small.
In addition, constant P0It can be set as maximum values or root of the value P (x, y) of the concentration distribution of contrast agent on direction in space
The arbitrary value determined according to experience.But if by constant P0It is set as the maximum value of the value P (x, y) of the concentration distribution than contrast agent
Small value, then sometimes through the calculating of formula (2) and coefficient k become the value bigger than 1.In this case, coefficient k is set as
1.
If also, to the pixel value that the distribution of each location of pixels (x, y) adjusts value by formula (1), can give birth to
Go out to parameterize image data made of blood vessel at the color and luminance portrayal with arrival phase and concentration corresponding to contrast agent.
In addition, the adjustment of brightness value shown in formula (1) can be executed when the color of color coding unit 23 encodes.
In this way, the parametrization image data generated in parameterizing image production part 21 can be with x-ray imaging picture number
It is similarly shown on a display device 14 according to, DSA image datas.In addition, as needed, can be preserved in video memory 16
Parameterize image data.
Fig. 7 is the figure of the example for the parametrization image for indicating to generate in parametrization image production part 21 shown in Fig. 1.
As shown in fig. 7, parametrization image, which becomes, shows the blood vessel for being filled with contrast agent with color and there is no radiographies
The image that brightness value is zero in the region of agent.In addition, blood vessel as the arrival time corresponding to contrast agent the area of color change
Domain is depicted.Therefore, it is possible to observe the case where blood flows together with contrast agent according to color.
It, can be in different date-times such ginseng shown in graph 7 repeatedly in order to observe the ongoing change of subject O
Numberization image.For example, if generating parametrization image before the treatment of subject O and after treatment, it can observe subject O's
Treatment is passed through.
That is, by according to the x-ray imaging image data being collected into mutually different period, generation conduct is performed a plurality of times
The image generation of the parametrization image data of phase image data is handled, and can obtain the first blood-vessel image data and the second blood
Pipe image data.Further, it is possible to the first blood-vessel image and the second blood-vessel image be shown, to be mutually compared diagosis.
But if the first blood-vessel image data and the second blood-vessel image data are compiled under conditions of different by color
Code, then corresponding phase is shown with different colors.Therefore, the comparison diagosis of blood-vessel image may become difficult.
Therefore, the colour synchronisation display processing portion 25 of parametrization image production part 21 is configured to, by color coding unit 23
And color range adjustment section 24 provides instruction information, to determine or correct the first blood-vessel image data and the second blood-vessel image data
At least one party pixel value so that between the first blood-vessel image data and the second blood-vessel image data corresponding phase pixel
Value is consistent.
For example, in the case where obtaining the first blood-vessel image data and newly-generated second blood-vessel image data in the past, it can
The pixel value corresponding to phase with the first blood-vessel image data matchingly determines that the phase institute of the second blood-vessel image data is right
The pixel value answered.In addition, it is generated in the first blood-vessel image data and the second blood-vessel image data both sides, it can
The pixel value of at least one party of the first blood-vessel image data and the second blood-vessel image data is corrected, so that the picture of corresponding phase
Element value is consistent.Below, it is assumed that the first blood-vessel image data are as past image data and before the second blood-vessel image data
It generates, is illustrated with this.
It can be manually selected over by the operation of operation bench 5 in the generation of the second blood-vessel image data or after generating
The first blood-vessel image data.Specifically, can by the operation of operation bench 5 retrieve video memory 16, select the past from
Same direction is using the parametrization image data that substantially identical conditions are photographed as the first blood-vessel image data.Alternatively, can also select
Select the source data of the x-ray imaging image data or DSA image datas of past time series as parametrization image data.
It is of course also possible to which the work(for automatically selecting past first blood-vessel image data is arranged in color burst display processing portion 25
Energy.It is automatic to obtain with same photography agreement or same for example, the past inspection information for same subject O can be retrieved
Camera angle and parametrization image data, the DSA image datas of time series or the X-ray of time series of camera positions photography
Image data.
Pass as the pixel value for making phase and color between the first blood-vessel image data and the second blood-vessel image data
It is consistent method, various methods can be enumerated.It can make phase and pixel value by different multiple methods
In the case of relationship consistency, multiple color synchronization patterns corresponding with method can be set.
Fig. 8 is to indicate according to the color range used in the generation of past first blood-vessel image data, decision or correct the
The figure of the example of the pixel value of two blood-vessel image data.
Fig. 8 (A) show over photography the first blood-vessel image data and make in the generation of the first blood-vessel image data
An example of color range.In addition, Fig. 8 (B) shows the second blood-vessel image data newly photographed and in the second blood-vessel image data
Generation in an example of color range for using.
As shown in figure 8, can be according to identical with the color range used in the generation of past first blood-vessel image data
Color range carries out the color coding of the second blood-vessel image data.In example shown in Fig. 8, using such to from opening shown in Fig. 5 (C)
It is assigned with color range made of the continuity variation of form and aspect during specified until terminating phase T2 of beginning phase T1.Certainly, exist
By such dullness shown in such color range or Fig. 3 (B) and Fig. 5 (B) with the variation of periodic form and aspect shown in Fig. 3 (C)
In the case of generation of the color range for the first blood-vessel image data, the color range with the variation of same form and aspect can be used to generate or repair
Positive second blood-vessel image data.
It is used in the generation of the first blood-vessel image data that is, colour synchronisation display processing portion 25 can be obtained for determining
The information of color range, the information based on acquirement and according to color identical with the color range used in the generation of the first blood-vessel image data
Rank, to determine or correct the pixel value of the second blood-vessel image data.In addition, can be from the incidental information of the first blood-vessel image data
The middle information obtained for determining the color range used in the generation of the first blood-vessel image data.Conversely, it can will be used for really
The information of the color range used in the generation of the first blood-vessel image data is scheduled on as the incidental information of the first blood-vessel image data and
It is stored in video memory 16 with the first blood-vessel image data.As a result, in the generation of the second blood-vessel image data, energy
It is enough to determine the color range used in the generation of the first blood-vessel image data.
If making the first blood-vessel image data that display is generated using common color range so side by side of display device 14 and the
Two blood-vessel image data then can be such that corresponding phase is shown with same color with very easy display processing.In addition, depositing
It, also can be with the phase and color with selected 1 blood-vessel image data in the case of 3 or more blood-vessel image data
Relationship consistency mode, adjust the phase of other blood-vessel image data and the relationship of color.
But it in the case that the different date-times waited before and after treatment carry out X-ray, is opened with the injection of contrast agent
The x-ray imaging image data of time series on the basis of moment beginning is not necessarily in the same period collected.In addition, in photography day
Between time phase for the position difference of the conduit (catheter) that injects contrast agent it is larger in the case of, contrast agent is to same position
The arrival time variation set.Thus, even same position, there is also the arrival phases of contrast agent in the first blood-vessel image data
Between the second blood-vessel image data other than treatment due to and the possibility that changes.In this case, even if using same
Color range, between the first blood-vessel image data and the second blood-vessel image data, same position is also shown in different colors.
It is thus possible to which corresponding when enough carrying out making between the first blood-vessel image data and the second blood-vessel image data repair
Just.Thereby, it is possible to so that same position is shown with same color between the first blood-vessel image data and the second blood-vessel image data.
In addition, correcting phase in order to make the solid colour of same position and being equivalent to not change phase and correct matching for color range
Color.Thus, at least one party of the pixel value by correcting phase and color range can make the color of the position not changed the
It is consistent between one blood-vessel image data and the second blood-vessel image data.The amendment of phase can carry out in color coding unit 23.
In addition, the amendment of the pixel value of color in color range can carry out in color range adjustment section 24.
Fig. 9 is to indicate to make the color in specified position or region in the first blood-vessel image data and the second blood-vessel image number
The figure of consistent example between.
Fig. 9 (A) indicate to make to depict the first blood-vessel image before the treatment of thrombus and eliminate after the treatment of thrombus the
The example that two blood-vessel images are shown side by side.As shown in Fig. 9 (A), for example, the first blood-vessel image number before the treatment of past photography
According to upper, the operation of operation bench 5 can be passed through and specify first position P1.If first position P1 does not change before and after treatment
Position, then preferably by the second of the first position P1 of the first blood-vessel image and the second blood-vessel image corresponding with first position P1
P2 is set to be shown with same color.
Therefore, it is possible to correct the first blood-vessel image data and the second blood-vessel image data at least one party pixel value,
So that in the first blood-vessel image data specify first position P1 first phase T (P1) in the second blood-vessel image data
The second phase T (P2) of the upper second position P2 corresponding to first position P1 becomes the correspondence that should be set as mutually the same pixel value
Phase.
Specifically, as described above, can correct phase and with when the side of color matching of corresponding color range or double
Side.In the case of only correcting phase, by make the phase of first position P1 and second position P2 when it is consistent in a manner of, amendment the
At least one party of one phase T (P1) and the second phase T (P2).On the other hand, in the case of only changing color range, so as to correspond to
The color of first phase T (P1) and the mode of the solid colour corresponding to the second phase T (P2) adjust color range.
Fig. 9 (B) expressions make between the first blood-vessel image data and the second blood-vessel image data color range common, simultaneously
Make the second phase T's (P2) of the second position P2 of the second blood-vessel image data and first position P1 of the first blood-vessel image data
The concentration distribution and corresponding color range of contrast agent in the case of consistent modified of first phase T (P1).It can be by Fig. 9 (B)
Dotted line shown in the second blood-vessel image data second position P2 contrast medium concentration distribution be modified to radiography shown in solid
Agent concentration is distributed.As shown in Fig. 9 (B), the amendment of the phase of certain position is visually equivalent to the parallel of contrast medium concentration distribution
It is mobile.Therefore, it is possible to make second position P2 color and first position P1 solid colour.
On the other hand, Fig. 9 (C) indicates the example for the case where substitution corrects phase and only corrects color range.In this case, correcting
Color range corresponding to the second blood-vessel image data is so that corresponding to the pixel value of the second phase T (P2) and corresponding to first phase
The pixel value of T (P1) is consistent.The form and aspect that the amendment of color range is visually equivalent to color range as shown in Fig. 9 (C) are continuous
The part of ground variation moves in parallel.
Region is specified alternatively, it is also possible to the position of substitution.In this case, the color matching of change phase or color range is so that represent
The pixel value in region is consistent.In addition, about the second position P2 corresponding to specified first position P1 or first area
Or second area, it can both be automatically detected, can also be manually specified by the operation of operation bench 5 according to coordinate information.
As the second position P2 or second automatically recognized corresponding to first position P1 specified manually or first area
The method in region, the method that the profile for the blood vessel that extraction is depicted with color can be enumerated.Specifically, can be in the first blood vessel
In image data, by image procossings such as edge extracting processing, the length for extracting one side centered on the P1 of first position is Δ
Rectangular area in blood vessel profile, and in the second blood-vessel image data search comprising extracted blood vessel profile square
Shape region.Further, it is possible to by the centre bit for the rectangular area that the length on 1 side detected in the second blood-vessel image data is Δ
It sets and is recognized as second position P2.The case where automatically recognizing second area corresponding with first area, as long as first area
It is smaller, then also it can recognize second area with same method.In addition, in the case where first area is larger, can be divided into
Multiple unit areas, and it is applicable in same method by per unit region.
In addition, in the example shown in Fig. 9 (B) and Fig. 9 (C), makes and indicate that the signal strength of contrast medium concentration is most
When corresponding pixel value when big value is consistent between the first blood-vessel image data and the second blood-vessel image data, but can use
Other methods seek the phase offset between concentration distribution.That is, between the maximum value of the concentration distribution of contrast agent can not be made
Phase difference is used as and answers modified phase offset, and so that the phase difference between concentration distribution is used as and answer modified phase offset.
Figure 10 be indicate using respectively with the first position P1 of the first blood-vessel image data and the second blood-vessel image data
The corresponding contrast agent of second position P2 concentration distribution a part seek the phase difference between concentration distribution example figure.
Figure 10 (A) is that display specifies the first blood-vessel image data of first position P1 and true side by side in the same manner as Fig. 9 (A)
The figure of the second blood-vessel image data of second position P2 corresponding with first position P1 is determined.
Figure 10 (B) is indicated the concentration distribution and the second blood of the contrast agent of the first position P1 of the first blood-vessel image data
The figure for the first case that the concentration distribution of the contrast agent of the second position P2 of pipe image data is compared.As shown in Figure 10 (B), lead to
The signal strength given threshold for crossing the concentration distribution of the contrast agent to first position P1 can extract arbitrary phase range delta T
Concentration distribution.
For example, when the prescribed limit centered on the phase by the signal strength of concentration distribution more than threshold value can be determined as
Phase range delta T.Such as threshold value can be determined as in advance to can be considered the value that contrast agent reaches.
On the other hand, the concentration distribution of the contrast agent of second position P2 can be made using offset to be parameter on phase direction
The offset when cross-correlation coefficient in extracted phase range delta T is maximum is sought in offset.If carrying out such optimization fortune
Calculate, then can calculate the offset Tshift of the concentration distribution of the contrast agent of second position P2 as between 2 concentration distributions when
Difference.
In addition, the replacement as cross-correlation coefficient, can also carry out indicating the well-behaved finger from amount using least squares error etc.
Target optimizes operation.Thus, according to index, sometimes also by the optimization operation for minimizing index, calculate between 2 concentration distributions
Phase difference.
Figure 10 (C) is the concentration for indicating the contrast agent by the concentration distribution of the contrast agent of first position P1 and second position P2
It is distributed the figure for the second case being compared.In blood flow situation very fast for the injection rate of contrast agent per unit time
Under, contrast agent is possible to be influenced by heart rate and reciprocal.In this case, the radiography as shown in Figure 10 (C) sometimes
The concentration distribution of agent becomes the curve of the waveform with multiple maximum.
If the concentration distribution execution to such wave mode shown in Figure 10 (C) makes cross-correlation coefficient maximumlly optimize operation,
The then cross-correlation coefficient increase and decrease corresponding to the offset of concentration distribution.Therefore, it is possible to obtain the offset of unsuitable phase
As optimal solution.
Therefore, it is more than initially the phase of threshold value by the signal strength of the concentration distribution of the contrast agent based on first position P1
Determine that the offset Tshift in the phase direction corresponding to phase range delta T and initial peak value by cross-correlation coefficient makees
For optimal solution, the phase difference appropriate between 2 concentration distributions can be calculated.
The computational methods of the phase difference of adjoint optimization operation in this way, can carry out the calculating of more accurate phase difference
And the amendment of phase.It is of course also possible to according to the phase difference found out, the amendment of such color range side shown in Fig. 9 (C) is carried out.
Also, repairing for one or both of phase and color range as described above can also be executed to whole location of pixels
Just.Thereby, it is possible to keep the color between the first blood-vessel image data and the second blood-vessel image data corresponding.That is, i.e. be used in by
In the case of the timing difference of the different situations or x-ray imaging photography in position of the conduit of contrast agent injection, as long as not having
The same position of variation, can also show the first blood-vessel image and the second blood-vessel image with same color.Therefore, the first blood vessel
The comparison diagosis of image and the second blood-vessel image becomes easy.
But in the photography of the first blood-vessel image data and when the photography of the second blood-vessel image data between due to tested
The reasons such as the heart rate number difference of body O and in the case of blood flow velocity difference, the change in flow of contrast agent.In this case, from making
The injection phase of shadow agent positions away from, the arrival Temporal variation of contrast agent according to the difference of the flow velocity of contrast agent.Thus, i.e.,
Make the amendment of progress as shown in Figure 9, the color at the same position not changed is in the first blood-vessel image and the second blood-vessel image
Between may also be different.In this case, multiple positions or region can be specified as the object for making solid colour.
Figure 11 is to indicate to make the color in 2 specified positions or region in the first blood-vessel image data and the second vessel graph
As the figure of example consistent between data.
Figure 11 (A) indicate to make to depict the first blood-vessel image before the treatment of thrombus and eliminate after the treatment of thrombus the
The example that two blood-vessel images are shown side by side.As shown in Figure 11 (A), such as can be in the first vessel graph before the treatment that the past photographs
As in data, by the operation of operation bench 5, other the third place P3 are also specified other than the P1 of first position.
If first position P1 and the third place P3 are the positions not changed before and after treatment, it is not only first
The second position P2 of the first position P1 of blood-vessel image and the second blood-vessel image corresponding with first position P1, for the first blood vessel
4th position P4 of the third place P3 of image and the second blood-vessel image corresponding with the third place P3 is it is also preferred that use same color
Display.
However, if in the photography of the first blood-vessel image, blood flow velocity is different when photography with the second blood-vessel image, i.e.,
Contrast agent is set to reach the phase of first position P1 and when consistent, the contrast agent arrival third position of contrast agent arrival second position P2
Phase and the phase of the 4th position P4 of contrast agent arrival for setting P3 are also inconsistent.
Therefore, it is possible to correct the first blood-vessel image data and the second blood-vessel image data at least one party pixel value,
So that other than first position P1 and second position P2, the third position that is further specified that in the first blood-vessel image data
Set P3 third phase T (P3) and in the second blood-vessel image data fourth position P4 corresponding with the third place P3 the 4th when
Phase T (P4) also becomes other corresponding phases.In addition, about the 4th position P4, it, being capable of hand also in the same manner as the P2 of the second position
Dynamic specified and automatic detection.In this case, pixel value can be corrected with interpolation processing, so that first position P1 and the
Each position between the phase and second position P2 and the 4th position P4 of each position between three position P3 when it is corresponding.
The object of interpolation processing is at least one party of the phase of phase and the form and aspect continuously changed in color range.At interpolation
In reason, the summary of processing can be realized by being set as linear interpolation.
In Figure 11 (B), Figure 11 (C), Figure 11 (D), Figure 11 (E), each longitudinal axis indicates signal corresponding with the concentration of contrast agent
Intensity S, each horizontal axis indicate phase T.In addition, Figure 11 (F) is indicated in the first blood-vessel image data and the second blood-vessel image data
Display in the color range that uses.
Figure 11 (B) to Figure 11 (E) expressions make color range be total between the first blood-vessel image data and the second blood-vessel image data
The concentration distribution of contrast agent in the case of phase logical, with the linear interpolation of phase to correct the second blood-vessel image data
Variation.In addition, the color range in the left side of the concentration distribution and Figure 11 (F) in left side corresponds to the first blood-vessel image data, right side
The color range on the right side of concentration distribution and Figure 11 (F) corresponds to the second blood-vessel image data.
First, it is corrected as first, executes each phase T for the whole positions for making the second blood-vessel image data in phase direction
The amendment of upper offset offset Δ T (P2), so that the second phase T (P2) of the second position P2 of the second blood-vessel image data becomes
The first phase T (P1) of the first position P1 of first blood-vessel image data.This, which is visually equivalent to, makes the second blood-vessel image number
According to the concentration distribution of contrast agent of each position offset up offset Δ T (P2) in phase side.
In Figure 11 (B), point of the first position P1 of the first blood-vessel image data is shown with dotted line and solid line in left side respectively
Cloth shows the distribution of the second position P2 of the second blood-vessel image data on right side and has carried out the first revised distribution.Together
In Figure 11 (C), the distribution of the third place P3 of the first blood-vessel image data is shown with dotted line and solid line in left side respectively for sample,
Right side shows the distribution of the 4th position P4 of the second blood-vessel image data and has carried out the first revised distribution.Here Δ
(P13) indicate that the time difference of T (P3) and T (P1), Δ (P24) indicate to T (P4) using the first revised result with T's (P1)
Time difference.
Then, corrected as second, if not due to narrow equal blood vessel states will because if Δ (P13) and Δ
(P24) it should be consistent.If without it is such will be because it may be considered that the difference be produced due to being due to the velocity variations of blood flow
It is raw, thus by the basis of T (P1) to T (P4) ' (=T (P4)-Δ T (P2)) be multiplied by Δ T (P13)/Δ T (P24), to carry out
It is flexible to correct.Distribution for the 4th position P4 of the second blood-vessel image data indicates to apply second on the right side of Figure 11 (D)
Revised result.
In conclusion the distribution of any position of the second blood-vessel image data is corrected with formula (3).That is, the second blood-vessel image
Phase data T2 ' when the when phase data T2 of data is corrected for.
T2 '={ T2- Δs T (P2)-T (P1) } { T (P3)-T (P1) }/{ T (P4)-T (P2) }+T (P1) (3)
If carrying out the interpolation processing of such phase, the first phase T of the first position P1 of the first blood-vessel image data
And the first blood-vessel image data (P1) unanimously with the second phase T (P2) of the second position P2 of the second blood-vessel image data,
The 4th phase T (P4) of the third phase T (P3) of the third place P3 and the 4th position P4 of the second blood-vessel image data is consistent.Cause
And if blood flow variation due to conduit alternate position spike exclusive or blood flow velocity, then by when phase data correcting process correct blood
The variation of stream.
But due to removing removing thrombus and in the case that the speed of blood flow changes before and after treatment, the variation of blood flow not by
It corrects.Therefore, as shown in Figure 11 (E), as a result, the 5th phase T of the 5th position P5 in the first blood-vessel image data
(P5) it with the revised phase T ' (P6) of the 6th phase T (P6) of the 6th position P6 of the second blood-vessel image data, can show
Go out effect of the larger difference as improving blood flow.
In addition, can also be carried out similarly by correcting the part that the form and aspect of color range continuously change as shown in Figure 9
The amendment of display color.In this case, visually, the part that the form and aspect of color range continuously change is parallel on phase direction
Mobile and dilatation.
In addition it is also possible to replace designated position as described above and specified region.In turn, using such shown in Fig. 3 (C)
The color range of such dullness shown in color range or Fig. 3 (B) and Fig. 5 (B) with the variation of periodical form and aspect generates the first blood-vessel image
In the case of data and the second blood-vessel image data, it also can similarly execute Fig. 9 or color range as shown in Figure 11 is timely
The synchronization process of phase.
It also can be by the way that directly specified manually respectively to the first blood-vessel image data and the second blood-vessel image data should be same
The phase section of step, to carry out the synchronous place of color range and phase between the first blood-vessel image data and the second blood-vessel image data
Reason.The phase section that should synchronize mutually and terminates phase at the beginning of capable of changing as the continuity of form and aspect and specify.
Figure 12 is the phase section for indicating to make to respectively specify that between the first blood-vessel image data and the second blood-vessel image data
Solid colour example figure.
Figure 12 (A) indicates the selection of the first DSA image datas or the first x-ray imaging image data by time series
Come the initial phase T11 for specifying the continuity of the form and aspect of color range to change and terminate examples of the phase T12 as first period.Separately
On the one hand, Figure 12 (B) indicates the selection of the 2nd DSA image datas or the second x-ray imaging image data by time series
Come the initial phase T21 for specifying the continuity of the form and aspect of color range to change and terminate examples of the phase T22 as the second phase.
In this case, at least one party of the first blood-vessel image data and the second blood-vessel image data can be determined or be corrected
Pixel value so as in order to generate the first blood-vessel image data and the company of the first pixel value of distribution of specified first period
Continuous property variation in order to generate the second blood-vessel image data and the continuity of the second pixel value of specified second phase distribution
Variation corresponds to.Specifically, the initial phase T21 of the pixel value and the second phase of initial phase T11 by making first period
Pixel value it is consistent and the cycle T scale1 of the variation of the first pixel value is set as to week with the variation of the second pixel value
Periods different phase Tscale2 can make the variation of the first pixel value corresponding with the variation of the second pixel value.Adjust the first pixel
The cycle T scale2 of the variation of the cycle T scale1 and the second pixel value of the variation of value so that the end phase of first period
The pixel value of T12 is consistent with the pixel value of end phase T22 of the second phase.
That is, by specifying phase manually, it can be by the color range of the first blood-vessel image data and the second blood-vessel image data
Color range is determined as, and phase is corresponding with the relationship of pixel value each other.Thus, if each initial phase T11, T21 is set as radiography
The inflow phase of agent, and by each maximum value or outflow phase for terminating phase T12, T22 and being set as the concentration of contrast agent, then it can be right
As comparison other phase interval selection execute color coded treatment.Further, it is possible to make pixel value relative to when phase region
Between length change rate it is consistent.As a result, it is possible to will not have between the first blood-vessel image data and the second blood-vessel image data
The same position of variation is shown with same color.
In addition, as other methods, following color synchronization processing can also be carried out：Pass through the DSA picture numbers of time series
According to or time series x-ray imaging image data selection, to the first blood-vessel image data and the second blood-vessel image data
Each initial phase T11, T21 of the difference only variation of specified pixel value, makes period of change Tscale1, Tscale2 of pixel value exist
It is common between first blood-vessel image data and the second blood-vessel image data.
Can by be used as on operation bench 5 Electronic Keying or hardkey (hard key) setting synchronous switch ON/OFF, come
Switch the synchronization process that various colors as described above are shown.In addition, the object for the synchronization process that color is shown can also
Enough it is set as the blood-vessel image data of 3 frames or more.That is, the operation by operation bench 5 can execute as follows, it is aobvious in color burst
In the case of showing that processing unit 25 has input the instruction that synchronous switch is switched to open state, colour synchronisation display processing portion 25 uses specified
Processing method executes multiple blood-vessel image data the synchronization process that color is shown, is had input in color burst display processing portion 25
In the case that synchronous switch is switched to the instruction of off status, it is able to carry out by each blood-vessel image data and independent color is aobvious
Show.
In addition, when synchronous switch becomes open state, in the case of being changed on the influential condition of color coding, colour synchronisation
Display processing portion 25 can follow the condition changed and execute the resynchronization process that color is shown.For example, shown in Figure 11 (A)
The 4th position P4, Figure 12 shown in terminate in the case that phase T12 is changed, can be with the 4th position P4, the knot after change
Shu Shixiang T12 execute the color coded treatment for simultaneous display as condition again.Further, it is possible to color in this way
Simultaneous display compares the multiple blood-vessel image data photographed in mutually different date-time, as color variation and regarding
The variation of blood flow is observed in feel.
The phase difference image making portion 26 of parametrization image production part 21 has the function of generating difference image data, the difference
Sub-image data is as parametrization image data and between the first blood-vessel image data and the second blood-vessel image data that generate
, with and the concentration of contrast agent become the difference image data of the corresponding pixel value of the difference of phase of specified conditions.That is, when
It differs in image making portion 26, sets each other off when can be tieed up by the 1st for being color coded to the first blood-vessel image data
Subtract shadow processing between maps mutually when the 2nd 2 for penetrating and being used for be color coded the second blood-vessel image data is tieed up, obtains two
The phase difference of dimension maps data.Also, color volume is carried out according to desirable color range by the way that two-dimensional phase difference is mapped data
Code can generate colored phase difference image data.That is, parametrization image of the phase difference image data as 2 frames can be generated
The difference image data of data.
In phase difference image data, the arrival of contrast agent between the first blood-vessel image data and the second blood-vessel image data
The data for the position that phase does not change are eliminated.Thus, only by the first blood-vessel image data and the second blood-vessel image data it
Between contrast agent arrival phase change part, i.e. occur ongoing change part be subject to color corresponding with variation degree
Display.Therefore, it is possible to quantitatively compare the first blood-vessel image data and the second blood-vessel image data.
Additionally, it is preferred that before subtracting shadow processing, by colour synchronisation display processing portion 25, execute for making the first blood-vessel image
The when corresponding phase correcting process of the phase of data and the second blood-vessel image data.Thereby, it is possible to cope with blood flow velocity
Difference etc..But only the different situation etc. of catheter position do not need phase section it is flexible it is modified in the case of, even if not by when
The correcting process of phase is executed as the pre-treatment for subtracting shadow processing, and can also generate has picture corresponding with the degree of ongoing change
The phase difference image data of element value.
In addition, the generation about phase difference image data is handled, switchs and compared with capable of similarly preparing with synchronous switch
Indicate whether to need to handle.In this case, in the case of having modified phase by the change by condition, it can also make phase difference
The amendment that image data follows phase is updated.
In having the function of above such and the radiographic apparatus 1 and medical image-processing apparatus 12 of structure, lead to
3 co-operating of camera chain 2 and control system is crossed, there is the conduct figure at least collecting x-ray imaging image data from subject O
As the function of collection system.In addition, the phase determining section 22 of parametrization image production part 21 and the collaboration of color coding unit 23 are dynamic
Make, is functioned as blood-vessel image generating unit, which is, based on what is be collected into mutually different period
Image generation processing is performed a plurality of times in x-ray imaging image data, to obtain the first blood-vessel image data and the second vessel graph
As data, described image generation processing is that the when phase transformation of the concentration of contrast agent is at least obtained based on x-ray imaging image data
Change, generated according to grayscale or color range have with the concentration of above-mentioned contrast agent become specified conditions when corresponding pixel value when
Phase images data.Such as the first blood can be obtained based on the x-ray imaging image data being collected into before the treatment of subject O
Pipe image data.On the other hand, for example, can based on the x-ray imaging image data being collected into after the treatment of subject O and
Obtain the second blood-vessel image data.
In turn, 25 co-operating of color coding unit 23, color range adjustment section 24 and colour synchronisation display processing portion, as pixel
Value determination section functions, which is to determine or correct the first blood-vessel image data and the second blood-vessel image
The pixel value of at least one party of data, so that corresponding phase between the first blood-vessel image data and the second blood-vessel image data
Pixel value it is consistent.
In addition, in pixel value determination section, the pixel value of blood-vessel image data can also be replaced and determine or correct phase
(time).In addition, in pixel value determination section, can also determine or correct blood-vessel image data pixel value and phase (when
Between) both sides.That is, in pixel value determination section, the pixel value and phase (time) of blood-vessel image data can be determined or corrected
At least one party.
On the other hand, phase difference image making portion 26 is functioned as difference image generating unit, which generates
Portion is, generate it is between the first blood-vessel image data and the second blood-vessel image data, with becoming specific with the concentration of contrast agent
The difference image data of the corresponding pixel value of difference of the phase of condition.
In addition, the color range adjustment section 24 of parametrization image production part 21 is played as pixel value scale (scale) generating unit
Function, the pixel value scale generating unit are that it is by the concentration-time variation to contrast agent is from initial time to finish time
The continuity variation of distribution pixel value is waited during being specified in during only and makes color range.
But as long as radiographic apparatus 1 and medical image-processing apparatus 12 have as same image collection system
The function of system, blood-vessel image generating unit, pixel value determination section and pixel value scale generating unit can pass through other compositions
Element constitutes radiographic apparatus 1 and medical image-processing apparatus 12.For example, can be by making computer reading make calculating
Machine handles journey as the medical imaging that blood-vessel image generating unit, pixel value determination section and pixel value scale generating unit function
Sequence constitutes medical image-processing apparatus 12.In this case, medical imaging processing routine is able to record in information recording carrier
It circulates as program product, so as to be used all-purpose computer as medical image-processing apparatus 12.
In the following, illustrating the action and effect of radiographic apparatus 1 and medical image-processing apparatus 12.Here, with right
First blood-vessel image data photographed to the second blood-vessel image data after being photographed and carry out color simultaneous display and
It is illustrated in case of the generation of phase difference image data.
Figure 13 is the action for indicating radiographic apparatus 1 shown in FIG. 1 and the processing in medical image-processing apparatus 12
Flow chart.
First, in step sl, the first X-ray image data is collected in a manner of non-radiography.Specifically, being in control
Camera chain 2 is moved to specified position under the control of system 3, and X is radiated from X-ray tube 6 towards the subject O for being set to diagnostic bed 10
Ray.Also, the X-ray for having transmitted subject O is collected as X-ray projection data by X-ray detector 7.By X-ray detection
The X-ray projection data that device 7 is collected into is handled to medical imaging by A/D converters 11 as the first X-ray image data and is filled
Set 12 outputs.
First X-ray image data can collect the amount of 1 frame, can also collect the amount of multiple frames.If collecting multiple frames
First X-ray image data of multiple frames is simultaneously carried out summation averaging by the first X-ray image data in filtering part 18, then can
Generate the non-radiography X-ray image data for 1 frame for reducing noise.Also, by the obtain in this way first non-radiography radioscopic image
Data are saved in video memory 16.
Then, in step s 2, the first x-ray imaging image data is continuously collected.For this purpose, in the control of control system 3
Under, contrast medium injection apparatus 15 acts, and injects contrast agent to subject O.Also, get over when being begun to pass through from the injection of contrast agent
The time first set then starts the photography of the first x-ray imaging image data.It is lasting to carry out also, during being determined in advance
The photography of first x-ray imaging image data.As a result, in video memory 16, the first X-ray of holding time sequence successively
Image data.In addition, the flow of the collection of the first x-ray imaging image data and the first non-radiography X-ray image data
Collection flow it is identical.
Then, in step s3, the first DSA image datas are generated by subtracting shadow portion 17.That is, by by the first non-radiography X
The shadow that subtracts that radiographic image data executes the first x-ray imaging image data of time series as mask images data is handled, according to
Secondary the first DSA image datas for generating time series.First DSA image datas of the time series of generation are saved in figure successively
As memory 16.
In addition, on a display device 14, the first x-ray imaging image of time series or the first DSA images can be made
It is shown in real time for realtime graphic (live image).Further, it is possible to by the first x-ray imaging image of time series
Or the first DSA images shown on a display device 14 after X-ray funeral affairs.The first DSA images are being shown afterwards
In the case of, it is carried out based on the first DSA image datas for subtracting shadow processing during phase that can be only specified to the operation by operation bench 5
Generation.
Then, in step s 4, by phase determining section 22, the time change of the first contrast medium concentration is obtained.It is specific and
Speech, by the first x-ray imaging image data or the first DSA of the time series during the specified phase of the operation by operation bench 5
Image data is taken into phase determining section 22.Also, in phase determining section 22 by each location of pixels come generate Fig. 3 (A) or
The concentration distribution of the time change of such concentration for indicating the first contrast agent shown in Fig. 5 (A).
In addition, the pre-treatment or post-processing of the generation of concentration distribution as contrast agent, it can be in filtering part 18 in sky
Between execute in one or both of direction and time orientation low-pass filtering treatment and rolling average processing one or both.
Thereby, it is possible to generate the concentration distribution for the smooth contrast agent for reducing noise.Correspondingly, in phase determining section 22, moreover it is possible to
Enough by interpolation processing, the calculating of center of gravity or curve matching, the shorter contrast agent of data break compared with the sampling interval is generated
Concentration distribution.
Then, in step s 5, by phase determining section 22, the concentration distribution based on contrast agent, by each location of pixels
To recognize the arrival phase of the first contrast agent.Specifically, can by the peak detection process of the concentration distribution to contrast agent,
The data processings such as threshold process are recognized the arrival phase of the first contrast agent by each location of pixels.
Alternatively, it is also possible to by the data processings such as peak detection process, threshold process recognize phase after, only to determining
Phase nearby during, execute the continuity concentration distribution based on interpolation processing, the calculating of center of gravity or curve matching acquirement.
In this case, to the continuity concentration distribution of acquirement, again by the data processings such as peak detection process, threshold process, detection
The arrival phase of real contrast agent.
Then, in step s 6, made in color range adjustment section 24 for being made found out by phase determining section 22 first
The first color range that the two-dimensional map of the arrival phase of shadow agent is color coded.In color range adjustment section 24, be not limited to Fig. 3 (B) with
And such form and aspect shown in Fig. 5 (B) vary continuously to the general color range of final phase with certain change rate from initial phase, such as
Shown in Fig. 3 (C) and Fig. 5 (C), the color range for making the change rate of the form and aspect of common color range increase can be made.
It makes in the case that such, form and aspect shown in Fig. 3 (C) are continuous and periodically variable color range, manipulation can be passed through
The operation of platform 5 determines the cycle T scale of form and aspect variation, and color range is made by making the form and aspect in 1 cycle T scale change.Or
The condition of these needs can also be previously set as default value by person.Furthermore it is possible to be arbitrarily designated opening in 1 cycle T scale
The form and aspect of beginning phase.In turn, in the form and aspect for the initial phase that the concentration for making contrast agent changes not since in 1 cycle T scale
In the case that the form and aspect of phase start, need it is specified with it is initial when corresponding form and aspect.
On the other hand, make shown in Fig. 5 (C) it is such, in specified phase during have and the specified phase phase
Between except different form and aspect continuity variation color range in the case of, can be divided by using the operation of operation bench 5 is specified
Match at the beginning of the continuity variation of form and aspect phase T1 and terminated phase T2 and makes color range.It can be by making display device 14
It shows the x-ray imaging image or DSA images of time series, and image is selected using the operation of operation bench 5, come when being started
Phase T1's and end phase T2 is specified.
Then, in the step s 7, executed based on the first color range made by color range adjustment section 24 in color coding unit 23
, the color coding of the two-dimensional map of the arrival phase of the first contrast agent.That is, according to color range, by the arrival with the first contrast agent
When corresponding R values, G values and B values distribute to each pixel as pixel value.The first parametrization image data is generated as a result,.
At this point, it is preferred that the corresponding coefficient of the concentration of contrast agent of arrival phase with the first contrast agent is multiplied by R values, G values
And B values.The brightness for the relatively high pixel of the concentration of the contrast agent of the arrival phase of the first contrast agent is generated as a result,
Brightness value is opposite for being worth the relatively small pixel of concentration of the contrast agent of arrival phase relatively large, whereas for contrast agent
The first smaller parametrization image data.
Further, it is possible to show the first parametrization image generated in this way on a display device 14.In addition it is possible to by making
First color range offsets up or stretches in phase side, and the first parametrization image is shown as dynamic image.Therefore, Yong Hutong
Observation the first parametrization image is crossed, is able to confirm that multiple blood vessels that contrast agent flows into.Especially since the form and aspect of the first color range
During variation is assigned to shorter phase, connect when so the arrival of contrast agent can be easily distinguished by the difference of color
Close multiple blood vessels.
If the photography of the first parametrization image terminates, treatment etc. can be implemented in step s 8.It then, can be with
The different date-time of date-time of photographing of one parametrization image, in order to which subject O starts the second parameter by observation
Change the photography of image.
In this case, in step S9 to step S13, with flow same as the first parametrization photography of image, obtain
2nd DSA images of the second non-radiography X-ray image data, the second x-ray imaging image data of time series, time series
The two-dimensional map data of the arrival phase of data, the time change of the second contrast medium concentration and the second contrast agent.
Also, in step S14, by color coding unit 23, color range adjustment section 24 and colour synchronisation display processing portion 25,
Execute between the making and the first parametrization image and the second parametrization image of corresponding with the first color range the second color range must
Want when match.Specifically, according to specified condition enactment method, that as illustrated in Fig. 8, Fig. 9, Figure 11 or Figure 12
Sample adjusts color range and phase one or both, so that when corresponding between the first parametrization image and the second parametrization image
The pixel value of phase is consistent.Thus, it is also possible to temporarily be generated according to cut-and-dried color range and show the second parametrization image data.
Then, in step S15, the two-dimensional map data of the arrival phase of the second contrast agent after phase is adjusted provide
To color coding unit 23.Also, in color coding unit 23, according to the second color range corresponding with the first color range, phase tune is executed
The color coded treatment of the two-dimensional map data of the arrival phase of the second contrast agent after whole.The second parametrization figure is generated as a result,
As data.
The the second parametrization image data generated is output to display device 14 together with the first parametrization image data.By
This, the first parametrization image and the second parametrization image are shown side by side on a display device 14.At this point, in the first parametrization figure
As between the second parametrization image, the pixel value of corresponding phase is consistent.Thus, it is shown in the first parametrization with same color
There is no the blood vessel of variation between image and the second parametrization image, the blood vessel changed is shown with different colours.Therefore, Yong Huneng
Ongoing change is enough observed by the difference of color.
Then, in step s 16, by phase difference image making portion 26, revised first contrast agent of phase is executed
Reach the two-dimensional map data of the two-dimensional map data of phase and the arrival phase of the second contrast agent subtracts shadow processing.It is tied
Fruit, only in the part of the arrival phase of contrast agent generation substantial variations, there are the two-dimensional phase differences of data to map data for acquirement.
Also, according to desirable color range to two-dimensional phase difference mapping Data Color coding in color coding unit 23.It generates as a result,
Colored phase difference image data.The phase difference image data of generation is shown on a display device 14.Therefore, user can lead to
The color for crossing phase difference image data visually carries out the quantitative assessment of ongoing change.
That is, in above such radiographic apparatus 1 and medical image-processing apparatus 12, pass through arriving contrast agent
Up to when equal determining phase with when corresponding color range be color coded, generate colored blood-stream image data, and energy
Enough adjust phase and color range, enabling be compared to each other multiple blood-stream image data in different date-time photographies.This
Outside, radiographic apparatus 1 and medical image-processing apparatus 12 by by the consecutive variations of the form and aspect of color range on phase direction
It reduces, improves the phase recognition capability based on color.
Therefore, according to radiographic apparatus 1 and medical image-processing apparatus 12, in different more of photography date-time
In a parametrization image, in the position of conduit of the photography periodically, for injecting contrast agent and blood flow velocity etc., conditions are different
In the case of, the position of the ongoing change based on treatment etc. can be also displayed without with same color.That is, can show side by side same
One color indicates the multiple parameters image of same phase actually actively.User can be different by photography date-time as a result,
Multiple parameters image be compared to each other.In turn, additionally it is possible to be shown, be carried out based on treatment by the color of phase difference image data
Deng ongoing change quantitative assessment.
Also, according to radiographic apparatus 1 and medical image-processing apparatus 12, even if radiography between adjacent blood vessel
The inflow phase of agent, reach phase or flow out phase difference it is small, can be used as the difference of form and aspect and easily distinguish blood vessel.
In particular, in the diagnosis of cerebral arteriovenous malformation or dural arteriovenous fistula, observe between artery and vein to disease
The blood flow flowing of affected part is important.It is then desired to distinguish multiple blood vessels of contrast agent inflow.But DSA images are due to ash
Rank shows, so being difficult to differentiate between radiography blood vessel.
In contrast, in radiographic apparatus 1 and medical image-processing apparatus 12, the form and aspect of color range can be become
The cycle match of change in the phase difference that should be identified it is shorter set.As a result, even if to concern multiple blood vessels almost simultaneously
Ground flows into contrast agent, also due to color presses each Vascular change, so as to be easy to carry out the differentiation of blood vessel.
More than, specific embodiment is recorded, but recorded embodiment is only an example and and unlimited
Surely the range invented.Here the new method and device recorded can be implemented in the form of various other.In addition, recording here
Method and device form in, without departing from the spirit of the invention, can carry out it is various omit, displacement and change.
Appended claims and its equivalent are as the content being contained in the scope and summary of invention, including such various forms
And variation.
For example, in the above-described embodiment, to generating blood-vessel image data as colored parametrization figure using color range
As the example of data is illustrated, but grayscale can also be utilized to generate blood-vessel image data.That is, can be according to grayscale or color range
Generate the phase image data and phase difference for having and becoming the time of specified conditions corresponding pixel value with the concentration of contrast agent
Image data.Furthermore it is possible to by pair with slave initial time to finish time of the time change of the concentration of contrast agent until
Period compared to the variation for distributing pixel value during shorter, to make grayscale or color range.
In the case of generating phase image data or phase difference image data using grayscale, as the variation of pixel value, take
For form and aspect variation and pair until slave initial time to finish time of the time change of the concentration of contrast agent during compared with
The continuity variation of brightness value is distributed during shorter.In this case, also can be by by system corresponding with the concentration of contrast agent
Number k is multiplied by brightness value, to which brightness value is set as value corresponding with the concentration of contrast agent.
Similarly, in the case of generating phase image data or phase difference image data using color range, as pixel value
Variation is not limited to the continuity variation of form and aspect as described above, can also distribute the continuity variation of brightness value.In this case,
It also can be by the way that coefficient k corresponding with the concentration of contrast agent be multiplied by brightness value, to which brightness value is set as dense with contrast agent
Spend corresponding value.
As described above, can by pair with slave initial time to finish time of the time change of the concentration of contrast agent until
During compared to the pixel value distributed during shorter variation, be set as the continuity variation of form and aspect, the brightness value of color company
The continuity variation of the brightness value of continuous property variation or grey.
In addition, in the above-described embodiment, instantiate X-ray tube 6 and X-ray detector 7 being fixed on C-arm 8
Both ends made of radiographic apparatus 1, but ginseng can be also equally generated in the radiographic apparatus constructed with other
Numberization image data.As the example of the radiographic apparatus constructed with other, in addition to having the radiodiagnosis of multiple arms
Device or have makes the X-ray for the mobile mechanism that arbitrary arm moves along the axis of any directions such as Arc Axial or linear axis examine
Other than disconnected device, it can also enumerate and examine the X-ray that X-ray tube 6 and X-ray detector 7 are separately fixed on independent arm
Disconnected device.In addition, in the case where X-ray tube 6 and X-ray detector 7 to be separately fixed on independent arm, to keeping X
First arm of ray tube 6 and keep the second arm of X-ray detector 7 be respectively set telescoping mechanism, rotating mechanism, articulation mechanism,
The driving mechanisms such as link mechanism are practical.
Claims (13)
1. a kind of medical image-processing apparatus, has：
Blood-vessel image generating unit at least obtains the Temporal variation of the concentration of contrast agent, and base based on x-ray imaging image data
In the x-ray imaging image data being collected into mutually different period, image generation processing is performed a plurality of times, to obtain first
Blood-vessel image data and the second blood-vessel image data, above-mentioned image generation processing are, according to grayscale or color range, generate have with
The concentration of above-mentioned contrast agent become specified conditions when corresponding pixel value phase image data；And
Pixel value determination section corrects at least one party's of above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data
Pixel value or phase so that between above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data, when corresponding
The pixel value of phase is consistent,
Above-mentioned pixel value determination section is configured to, and corrects above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data
The pixel value or phase of at least one party so that the first area or first position specified in the above-mentioned first blood-vessel image data
First phase and the second area corresponding with above-mentioned first area or above-mentioned first position in above-mentioned second blood-vessel image data
Or the second phase of the second position, become above-mentioned corresponding phase.
2. such as the medical image-processing apparatus that claim 1 is recorded,
Above-mentioned pixel value determination section is configured to, and above-mentioned first blood-vessel image data and above-mentioned second are corrected with interpolation processing
The pixel value or phase of at least one party of blood-vessel image data so that further specified that in above-mentioned first blood-vessel image data
The third phase of third region or the third place and in above-mentioned second blood-vessel image data with above-mentioned third region or above-mentioned
The corresponding the fourth region in three positions or the 4th phase of the 4th position become other above-mentioned corresponding phase, also, above-mentioned
Phase and above-mentioned second area between one region or above-mentioned first position and above-mentioned third region or above-mentioned the third place or on
State between the second position and above-mentioned the fourth region or above-mentioned 4th position when it is corresponding.
3. a kind of medical image-processing apparatus, has：
Blood-vessel image generating unit at least obtains the Temporal variation of the concentration of contrast agent, and base based on x-ray imaging image data
In the x-ray imaging image data being collected into mutually different period, image generation processing is performed a plurality of times, to obtain first
Blood-vessel image data and the second blood-vessel image data, above-mentioned image generation processing are, according to grayscale or color range, generate have with
The concentration of above-mentioned contrast agent become specified conditions when corresponding pixel value phase image data；
Pixel value determination section corrects at least one party's of above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data
Pixel value or phase so that between above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data, when corresponding
The pixel value of phase is consistent；And
Pixel value scale generating unit, the pixel value scale generating unit is by the Temporal variation of the concentration to above-mentioned contrast agent from first
Beginning phase until terminating phase during in specify during distribute pixel value continuity variation, come make above-mentioned grayscale or
Above-mentioned color range,
Above-mentioned pixel value determination section is configured to, and corrects above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data
At least one party, pixel value or phase at least one party so as to specified in order to generate above-mentioned first blood-vessel image data
The continuity of first pixel value of first period distribution changes and to specified in order to generate above-mentioned second blood-vessel image data
The continuity variation of second pixel value of second phase distribution corresponds to,
Also, above-mentioned pixel value determination section is configured to, the pixel value and above-mentioned the of the initial phase by making above-mentioned first period
The pixel value of initial phase during two is consistent, and is and above-mentioned second by the cycle set of the variation of above-mentioned first pixel value
Different period in period of the variation of pixel value, come make above-mentioned first pixel value variation and above-mentioned second pixel value variation pair
It answers.
4. a kind of medical image-processing apparatus, has：
Blood-vessel image generating unit at least obtains the Temporal variation of the concentration of contrast agent, and base based on x-ray imaging image data
In the x-ray imaging image data being collected into mutually different period, image generation processing is performed a plurality of times, to obtain first
Blood-vessel image data and the second blood-vessel image data, above-mentioned image generation processing are, according to grayscale or color range, generate have with
The concentration of above-mentioned contrast agent become specified conditions when corresponding pixel value phase image data；And
Difference image generating unit, generate it is between above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data, have
And the concentration of above-mentioned contrast agent becomes the difference image data of the corresponding pixel value of the difference of phase of specified conditions.
5. such as the medical image-processing apparatus that claim 4 is recorded,
It is also equipped with pixel value determination section, determines or correct above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data
At least one party pixel value or phase so that above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data it
Between, the pixel value of corresponding phase is consistent.
6. such as the medical image-processing apparatus that claim 5 is recorded,
Above-mentioned pixel value determination section is configured to, and obtains for determining the ash used in the generation of above-mentioned first blood-vessel image data
The information of rank or color range is used based on acquired above- mentioned information according to in the generation of above-mentioned first blood-vessel image data
Above-mentioned grayscale or the identical grayscale of above-mentioned color range or color range, determine or correct the pixel value of above-mentioned second blood-vessel image data.
7. such as the medical image-processing apparatus that claim 5 is recorded,
It is also equipped with pixel value scale generating unit, the Temporal variation which passes through the concentration to above-mentioned contrast agent
Specify from during initial phase is until terminating phase during distribute the continuity variation of pixel value, it is above-mentioned to make
Grayscale or above-mentioned color range,
Above-mentioned pixel value determination section is configured to, and corrects above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data
At least one party, pixel value or phase at least one party so as to specified in order to generate above-mentioned first blood-vessel image data
The continuity of first pixel value of first period distribution changes and to specified in order to generate above-mentioned second blood-vessel image data
The continuity variation of second pixel value of second phase distribution corresponds to.
8. such as the medical image-processing apparatus that any one of claim 1 to 7 is recorded,
Above-mentioned blood-vessel image generating unit is configured to, and generates upper when having the concentration with above-mentioned contrast agent as above-mentioned specified conditions
State the phase image data of the corresponding brightness value of concentration of contrast agent.
9. such as the medical image-processing apparatus that any one of claim 1 to 7 is recorded,
Above-mentioned blood-vessel image generating unit is configured to, by the regulation ratio of the concentration become the maximum of above-mentioned contrast agent, above-mentioned maximum value
Example or threshold value time as become above-mentioned specified conditions time, to generate above-mentioned phase image data.
10. such as the medical image-processing apparatus that any one of claim 1 to 7 is recorded,
Above-mentioned blood-vessel image generating unit is configured to, based on the data break that the sampling interval with the concentration than above-mentioned contrast agent is short
, the time change of the concentration of contrast agent, generating has that become the time of specified conditions with the concentration of above-mentioned contrast agent corresponding
The above-mentioned phase image data of above-mentioned pixel value.
11. such as the medical image-processing apparatus that claim 3 or 7 is recorded,
Above-mentioned pixel value scale generating unit distributes continuity variation, the color of form and aspect by the variation as above-mentioned pixel value
Brightness value continuity variation or grey brightness value continuity variation, to make above-mentioned grayscale or above-mentioned color range.
12. such as the medical image-processing apparatus that any one of claim 1 to 7 is recorded,
Above-mentioned blood-vessel image generating unit is configured to, and based on the x-ray imaging image data being collected into before the treatment of subject, takes
Above-mentioned first blood-vessel image data are obtained, based on the x-ray imaging image data being collected into after the treatment of above-mentioned subject, are obtained
Above-mentioned second blood-vessel image data.
13. a kind of radiographic apparatus, has：
Image collection system at least collects x-ray imaging image data from subject；
Blood-vessel image generating unit obtains the Temporal variation of the concentration of contrast agent, and base based on above-mentioned x-ray imaging image data
In the x-ray imaging image data being collected into mutually different period, image generation processing is performed a plurality of times, to obtain first
Blood-vessel image data and the second blood-vessel image data, above-mentioned image generation processing are, according to grayscale or color range, generate have with
The concentration of above-mentioned contrast agent become specified conditions when corresponding pixel value phase image data；And
Pixel value determination section corrects at least one party's of above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data
Pixel value or phase so that between above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data, when corresponding
The pixel value of phase is consistent,
Above-mentioned pixel value determination section is configured to, and corrects above-mentioned first blood-vessel image data and above-mentioned second blood-vessel image data
The pixel value or phase of at least one party so that the first area or first position specified in the above-mentioned first blood-vessel image data
First phase and the second area corresponding with above-mentioned first area or above-mentioned first position in above-mentioned second blood-vessel image data
Or the second phase of the second position, become above-mentioned corresponding phase.
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| JP2013081571A JP6173751B2 (en) | 2013-04-09 | 2013-04-09 | Medical image processing apparatus, X-ray diagnostic apparatus, and medical image processing program |
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| JP6222807B2 (en) * | 2013-04-01 | 2017-11-01 | 東芝メディカルシステムズ株式会社 | Medical image processing apparatus, X-ray diagnostic apparatus, and medical image processing program |
| JP6338849B2 (en) * | 2013-12-11 | 2018-06-06 | キヤノンメディカルシステムズ株式会社 | Image analysis apparatus and X-ray diagnostic apparatus |
| JP6392040B2 (en) * | 2014-09-11 | 2018-09-19 | キヤノンメディカルシステムズ株式会社 | Image processing apparatus and X-ray diagnostic apparatus |
| JP6537797B2 (en) * | 2014-09-29 | 2019-07-03 | キヤノンメディカルシステムズ株式会社 | Medical image processing apparatus and X-ray diagnostic apparatus |
| WO2016084373A1 (en) * | 2014-11-27 | 2016-06-02 | 国立大学法人広島大学 | Simulator, injection device or imaging system provided with simulator, and simulation program |
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| JP6590503B2 (en) * | 2015-04-01 | 2019-10-16 | キヤノン株式会社 | Photoacoustic apparatus and information acquisition apparatus |
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| JP2017099616A (en) * | 2015-12-01 | 2017-06-08 | ソニー株式会社 | Surgical control device, surgical control method and program, and surgical system |
| JP6758951B2 (en) | 2016-06-28 | 2020-09-23 | 国立大学法人東北大学 | X-ray diagnostic equipment, image processing equipment, and diagnostic imaging support method |
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| RU2633949C1 (en) * | 2016-08-03 | 2017-10-19 | Закрытое Акционерное Общество "Импульс" | Method for generating composite image from series of angiographic digital subtraction frames |
| JP7159160B2 (en) | 2016-12-15 | 2022-10-24 | コーニンクレッカ フィリップス エヌ ヴェ | Visualization of vascular structures |
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